Stent

ABSTRACT

A stent comprising a stent body and a plurality of cells is disclosed. Each cell includes two structural members extending in an undulating pattern. Each structural member includes a plurality of cell segments defining a plurality of peaks and valleys therebetween. A first segment and a second segment defining a first peak, the second segment and a third segment defining a first valley, the third segment and a fourth segment defining a second peak, the fourth segment and a fifth segment defining a second valley, the fifth segment and a sixth segment defining a third peak. The first peak, the second peak and the first valley include a first radius of curvature. The third peak and the second valley include a second radius of curvature. The first radius of curvature is larger than the second radius of curvature.

This application is a continuation of U.S. patent application Ser. No. 13/834,840, filed Mar. 15, 2013 by Vogel et al., the entire content of which is incorporated herein by reference.

BACKGROUND

1. Technical Field

The present disclosure relates generally to stents, and, in particular, relates to stents having nodes with particular radii of curvatures.

2. Description of Related Art

Stents are widely used for numerous applications where the stent is placed in the lumen of a patient and expanded. Such stents may be used in coronary or other vasculature, as well as other body lumens.

Commonly, stents are cylindrical members. The stents expand from reduced diameters to enlarged diameters. Stents may either be self-expanding or balloon-expandable. Self-expanding stents are generally inserted into vasculature via a delivery device; the removal of the delivery device causes the stent to radially expand. Balloon-expandable stents are placed on a balloon catheter with the stent in the reduced-diameter state. So placed, the stent is advanced on the catheter to a placement site. At the site, the balloon is inflated to expand the stent to the enlarged diameter. The balloon is deflated and removed, leaving the enlarged diameter stent in place. So used, such stents are used to substantially retain or expand diameters of occluded sites within a patient's vasculature or other lumen.

Examples of stents are numerous. For example, U.S. Pat. No. 5,449,373 to Pinchasik et al. teaches a stent with at least two rigid segments joined by a flexible connector. U.S. Pat. No. 5,695,516 to Fischell teaches a stent with a cell having a butterfly shape when the stent is in a reduced-diameter state. Upon expansion of the stent, the cell assumes a hexagonal shape.

When stents are placed in certain parts of the body, it may be desirable for the stent to be both strong and flexible. For example, when a stent is placed within a patient's vasculature at or near a patient's joint (e.g., hip, knee, elbow, etc.), the stent may be bent often and may be subject to a relatively large amount of mechanical strain. Thus, a stent that is both flexible and strong may be desirable for use in these and other instances.

SUMMARY

The present disclosure relates to a stent comprising a stent body and a plurality of cells. Each cell includes two structural members extending in an undulating pattern. Each structural member includes a plurality of cell segments defining a plurality of nodes therebetween. The radius of curvature of a first node is different from the radius of curvature of a second node.

In disclosed embodiments, the radius of curvature of the first node is between about 200% and about 700% larger than the radius of curvature of the second node.

In disclosed embodiments, the radius of curvature of the first node is between about 500% and about 600% larger than the radius of curvature of the second node.

In disclosed embodiments, the radius of curvature of the first node is about 250% larger than the radius of curvature of the second node.

In disclosed embodiments, the radius of curvature of the first node is between about 0.0030 inches and about 0.0040 inches. Here, it is envisioned that the radius of curvature of the second node is between about 0.0001 inches and about 0.0010 inches.

In disclosed embodiments, the stent body includes a predeployed inside diameter of between about 0.0500 inches and about 0.0600 inches.

The present disclosure also relates to a stent comprising a stent body defining a length and comprising a plurality of cells. Each cell comprises two structural members extending in an undulating pattern. Each structural member comprises a plurality of cell segments defining a plurality of peaks of valleys therebetween. A first segment and a second segment define a first peak. The second segment and a third segment define a first valley. The third segment and a fourth segment define a second peak. The fourth segment and a fifth segment define a second valley. The fifth segment and a sixth segment define a third peak. The first peak and the first valley include a first radius of curvature, and the second peak, the third peak and the second valley include a second radius of curvature. The first radius of curvature is larger than the second radius of curvature.

In disclosed embodiments, the first radius of curvature is between about 200% and about 700% larger than the second radius of curvature.

In disclosed embodiments, the first radius of curvature is between about 500% and about 600% larger than the second radius of curvature.

In disclosed embodiments, the first radius of curvature is about 250% larger than the second radius of curvature.

In disclosed embodiments, the first radius of curvature is between about 0.0030 inches and about 0.0040 inches. Here, it is disclosed that the second curvature is between about 0.0001 inches and about 0.0010 inches.

In disclosed embodiments, each structural member includes a seventh segment and an eighth segment. The sixth segment and the seventh segment define a third valley. The seventh segment and the eighth segment define a fourth peak. The third valley includes the second radius of curvature, and the fourth peak includes the first radius of curvature. Here, it is disclosed that the first radius of curvature is between about 200% and about 700% larger than the second radius of curvature.

In disclosed embodiments, the first radius of curvature is between about 0.0030 inches and about 0.0040 inches, and the second radius of curvature is between about 0.0001 inches and about 0.0010 inches. Here, it is disclosed that the stent body includes a predeployed inside diameter of between about 0.0500 inches and about 0.0600 inches.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the present disclosure will be readily appreciated by reference to the drawings wherein:

FIG. 1 is a plan view of a stent according to an embodiment of the present disclosure as it would appear if it were longitudinally split and laid out flat;

FIGS. 2 and 3 are enlarged views of portions of the stent of FIG. 1;

FIG. 4 is a plan view of a portion of the stent of FIG. 1 in a deployed/expanded orientation, the stent has been longitudinally cut and laid flat; and

FIGS. 5 and 6 are enlarged views of portions of the stent shown in FIG. 4.

DESCRIPTION

In the following description, the terms “proximal” and “distal” as used herein refer to a direction or a position along a longitudinal axis of a catheter or medical instrument. The “proximal” or “trailing” end of the instrument is generally the segment of the instrument that is closest to the clinician or to the entrance site into a body. The “distal” or “leading” end of the instrument is generally the segment of the instrument placed farthest into a body lumen from the entrance site. Additionally, the term “preloaded” relates to the configuration of the stent prior to the stent being loaded into a catheter, and the term “predeployed” relates to the configuration of the stent while the stent is compacted into the catheter.

The stent of the present disclosure has particular application in the vasculature of a patient where it is subject to a relatively high amount of strain and movement. For example, the disclosed stent may be suitable for use within the vasculature of a patient's hip area, e.g., to help reduce problems associated with a deep vein thrombosis (DVT). However, the disclosed stent may be used in any interventional, diagnostic, and/or therapeutic procedure. The stent may be a component of an apparatus or system used in conjunction with any of the above applications.

The various embodiments of the disclosure will now be described in connection with the drawings. It should be understood that for purposes of better describing the disclosure, the drawings may not be to scale. Further, some of the figures may include enlarged or distorted portions for the purpose of showing features that would not otherwise be apparent.

With initial reference to FIG. 1, the present disclosure includes a stent 100. Stent 100 may be expanded from a rest diameter (and corresponding a rest circumference) to an expanded or enlarged diameter. While stent 100 is generally used when in a cylindrical configuration, for ease of illustration FIG. 1 illustrates a stent 100 in a flattened condition. Moreover, FIG. 1 shows stent 100 cut longitudinally along its length L and laid flat, and is representative of the stent 100 after stent 100 has been laser cut from a shape-memory tube, for instance, but before stent 100 has been shape-set to the expanded diameter. FIG. 4 shows a portion of the stent 100 after the stent has been shape-set to the desired expanded diameter. In both FIGS. 1 and 4, the stent 100 extends along elongated axis A-A and includes a stent body (i.e., a three-dimensional structure) having cell defining portions that define a plurality of cells 120, which are bounded areas which are open (i.e., extend through the wall thickness of the stent 100). After the stent 100 has been shape-set to the expanded diameter D as shown in FIG. 4, the cells 120 are generally more open than the cells depicted in FIG. 1.

With continued reference to FIG. 4, cells 120 have a longitudinal or major axis X_(M)-X_(M) and a transverse or minor axis X_(m)-X_(m); the major axis of the cell X_(M)-X_(M) is perpendicular to the longitudinal axis A-A of stent 100. In disclosed embodiments, cell 120 may be repeated throughout a least a portion of the length L and the diameter D of the stent 100 (i.e., each cell 120 may be substantially identical to other cells 120).

Referring to FIGS. 2 and 3, which are enlarged portions of the stent 100 of FIG. 1, the cell defining portions of stent 100 include first connection locations 130 and second connection locations 132. First and second connection locations 130, 132 are where circumferentially adjacent cell defining structures, as defined relative to axis A-A, are connected together, and where longitudinally adjacent cell defining portions, as defined relative to the axis A-A, are connected together.

With particular reference to FIG. 4, cells 120 are defined by portions of the tube material and include first and second longitudinal segments 140 a and 140 b, collectively referred to as cell segments 140. With additional reference to FIGS. 3 and 6, each of which illustrates half of a cell 120, each cell segment 140 has an undulating pattern which defines a plurality of peaks 150, 152, 154, 156 and valleys 160, 162, 164. The peaks 150, 152, 154, 156 are spaced outwardly or away from the longitudinal axis X_(M)-X_(M), and the valleys 160, 162, 164 are spaced inwardly or toward the longitudinal axis X_(M)-X_(M).

FIGS. 3 and 6 are enlarged portions of a stent illustrating certain aspects of a stent design that can be optimized based on the desired performance of the stent. Each cell segment 140 is shown including: 1) a first segment 141 that extends from a first connection location 130 a to peak 150; 2) a second segment 142 that extends from peak 150 to valley 160; 3) a third segment 143 that extends from valley 160 to peak 152; 4) a fourth segment 144 that extends from peak 152 to valley 162; 5) a fifth segment 145 that extends from valley 162 to peak 154; 6) a sixth segment 146 that extends from peak 154 to valley 164; 7) a seventh segment 147 that extends from valley 164 to peak 156; and 8) an eighth segment 148 that extends from peak 156 to a second connection location 130 b. Additionally, as shown in FIG. 6, peak 152 is part of connection location 132. Collectively, peaks and valleys are referred to herein as nodes.

In the illustrated embodiment, segments 141-148 extend generally longitudinally along stent 100. The term “generally longitudinally” will be understood to mean that segments 141-148 are closer to a parallel relationship relative to the axis A-A of stent 100 (e.g., FIG. 3) than to a transverse relationship relative to the axis A-A of stent 100.

Each node comprises a generally semi-circular arcuate segment including a radius of curvature “R_(S)”, a length “L_(S)” (along axis A-A), and a width “W_(S)” (perpendicular to axis A-A) (see FIG. 3). The radius of curvature “R_(S)” is defined as the distance of the circular arc which best approximates the curve at that point, and is measured along an inside edge of the node, as shown in FIG. 3. In disclosed embodiments, peak 150 and valley 160 may comprise a radius of curvature between about 0.00300 inches and about 0.00400 inches (e.g., equal to about 0.00318 inches). In disclosed embodiments, the valley 162, peak 152, peak 154, valley 164, and peak 156 may comprise a radius of curvature between about 0.0001 inches and about 0.0010 inches (e.g., equal to about 0.0005 inches). Moreover, it is envisioned that the radii of curvature of peak 150 and valley 160 are equal or substantially equal to each other, and it is envisioned that the radii of curvature of each of valley 162, peak 152, peak 154, valley 164, and peak 156 are equal or substantially equal to each other. It is further disclosed that any peak and any valley of each cell 120 can have any of the disclosed radii of curvature.

In one embodiment, a stent may have more than two distinct radii of curvature within each cell 120. By way of non-limiting example, it can be envisioned that stent 100 includes cells 120 where a larger (or largest) radius of curvature between adjacent nodes is between about 200% and about 700% (e.g., approximately 250%) larger than the smaller (or smallest) radius of curvature between adjacent nodes.

The width of peak 150 and valley 160 may be between about 0.0250 inches and about 0.0265 inches (e.g., equal to about 0.0258 inches). The width of valley 162, peak 152, peak 154, valley 164 and peak 156 may be between about 0.0240 inches and about 0.0250 inches (e.g., equal to about 0.0245 inches). It is further envisioned that any peak and any valley of each cell 120 can have any of the disclosed widths.

The length of peak 150 and valley 160 may be between about 0.0150 inches and about 0.0170 inches (e.g., equal to about 0.0160 inches). The length of valley 162, peak 152, peak 154, valley 164 and peak 156 may be between about 0.0150 inches and about 0.0170 inches (e.g., equal to about 0.0160 inches). It is further envisioned that any peak and any valley of each cell 120 may have any of the described lengths. The width “W_(CP)” of connecting portions 130 and 132 (see FIG. 5) may be between about 0.0100 inches and about 0.0200 inches (e.g., equal to about 0.0149 inches).

As discussed hereinabove, the stent 100 includes cells 120 having multiple nodes, wherein at least one node has a different radius from the other nodes. It is envisioned that these features help extend the life and/or durability of the disclosed stent 100. For example, the mechanical strains undergone by stent 100 when stent 100 is within a patient's vasculature (e.g., within a region subject to repeated joint flexure) results in a more balanced distribution of strains versus a typical stent where each node has the same radius, for example. A combination of finite element analysis, durability testing, fatigue testing, and repeating bending load testing may be performed to help determine the ranges of dimensions for each node and to tune the desired performance of a given stent 100. For example, to help balance the strains undergone by stent, the radius of the node that experiences the highest strains during testing (e.g., finite element analysis, durability testing, fatigue testing, and/or repeating bending load testing) is increased. If/when a different node experiences the highest strains during a subsequent test, the radius of that node is increased. This testing process is repeated until the strength and/or size of the compacted diameter become unacceptable for its desired application, and/or until additional increases in node radius provides negligible additional improvement in strength or durability.

When stent 100 is compacted into the catheter (i.e., its predeployed configuration), the diameter of stent 100 is reduced as compared to when stent 100 has not yet been loaded into the catheter (i.e., its preloaded configuration). This associated reduction in stent circumference is accommodated by reduction in the angles between segments which results in an increase in bending strain (e.g., especially adjacent nodes). As the cell is deformed (e.g., when stent 100 is loaded into catheter, or when the delivery system is navigating through the vasculature to the treatment site), especially during bending or axial loading, certain angles between adjacent segments increase or decrease more than others due to the lack of symmetry inherent in most flexible stent designs. As a result, there is a greater amount of strain in the nodes that connect those adjacent segments. The amount of strain concentrated near the nodes can be calculated using finite element analysis, for example.

The maximum strain in a deformed stent is called the peak strain. The peak strain typically occurs in a single segment in the vicinity of a node although it may occur elsewhere in the stent depending on the stent design. Predominant strains in stents may be tensile (usually defined as positive) or compressive (usually defined as negative). Strains can be categorized as being of two kinds: normal strains and shear strains. Normal strains can be positive (e.g., tensile) or negative (e.g., compressive). There are positive and negative shear strains as well, but in this case the sign convention is arbitrary, and physically there is no real difference between positive and negative shear strains. Normal strains, which are also referred to as principal strains, are generally the basis for strain analysis and durability analysis of stents.

High tensile strains may cause cracks to initiate and propagate through the stent, leading to reduced fatigue life and stent fracture (i.e., failure mode). Compressive strains do not tend to cause cracks, and so generally do not cause reduced stent life unless the magnitude of the strain is extraordinary. Some portions of a deformed stent may be highly strained during use while other portions may not be strained at all. A deformed stent can be thought of as a collection of tiny volumetric regions, each region having a strain level; collectively, the strain levels of the regions range from a maximum negative value to a maximum positive value. For a stent in service in the body, if stent strains are maintained below the endurance limit of the stent material then high fatigue life may be expected assuming the stent material has undergone proper materials processing and surface finishing. However, if a stent in service in the body suffers stent strains above the endurance limit of the stent material then high fatigue life cannot be expected regardless of stent material processing and surface finishing.

Commonly, stents are designed such that the strain in the stent remains at a low level under pulsatile loading conditions, i.e. under oscillating circumferential compressive strains. However, it has been determined that stents implanted in other locations, for example within a patient's vasculature at or near a patient's joint, can subject a stent to larger amounts of strain than previously predicted.

Bending and any associated elongation of stent 100 results in concentration of tensile strains at and within particular nodes thereby exposing the segments near or adjacent the nodes, and the nodes themselves, to lower fatigue life. Concentration of compressive strains in other nodes permit the segments near or adjacent those nodes to sustain higher fatigue life. As such, balancing the strains experienced by the stent 100 increases the overall fatigue life of stent 100. Balancing the strain may involve changing the design of the stent 100 such that the nodes that are otherwise exposed to higher levels of tensile strains have a way to distribute that strain to help improve the fatigue life of the particular node and adjacent segments, and thus, help improve the fatigue life of the entire stent 100.

The stent 100 of the present disclosure helps balance the strain by providing nodes with different radii of curvature from one another. As the strain is concentrated in regions where the radius of curvature is the smallest, it follows that by increasing the radius, the peak strain is reduced. The nodes of each cell that undergo the larger amount of strain have a larger radius associated therewith. Thus, nodes having the larger radius of curvature have a lower amount of peak strain associated therewith, and which thus improves fatigue life (i.e., helps prevent the stent from breaking). Further, the particular nodes of stent 100 that include a larger radius of curvature are the nodes that were found to undergo the highest peak strains during various testing procedures. Therefore, the overall life and performance of the stent is improved.

However, while altering the radii of various nodes may improve certain aspects of the stent design, such changing of radii may decrease the strength of at least part of the stent. More particularly, stent 100 is compacted to a relatively small diameter in order to enable stent 100 to fit into a delivery system that travels through a patient's vasculature. Generally, as the node radius increases and the segment widths remain constant, the minimum compaction diameter increases in proportion to the increase in radius. If the required compaction diameter is desired to be a fixed amount, then as the node radius is increased, the segment widths would have to decrease. This decrease in segment width may lead to a decrease in stent strength. Thus, for each stent design and desired application, it is possible to tune the overall stent design to ensure the durability benefits outweigh the loss of strength or an increase in compaction diameter due to increasing the node radius. By way of a non-limiting example, for venous stents (as compared to arterial stents) the diameter of the delivery system may be less critical for two reasons: 1) veins generally have larger diameters than arteries; and 2) blood pressure is lower in veins versus arteries, so the size of an access hole made to get the delivery device into a vein may be less critical, as once the procedure is complete, it is easier to stop the bleeding from a hole in a vein than in an artery. Thus, the design of a stent can be tuned for a venous application by considering the desired strength of the stent, the desired durability, and the desired size of its compacted diameter, along with the interplay between these criteria.

It is further envisioned that in addition to stent 100 having nodes with different radii of curvature from one another, at least one node of stent 100 includes a non-constant radius of curvature. In certain situations, a stent having a combination of nodes with different radii of curvature and with non-constant radii of curvature may further augment the balanced distribution of forces. Further details of stents having nodes with a non-constant radius of curvature is disclosed in U.S. application Ser. No. ______ (Attorney Docket No. H-KN-02622 (1847-141)), filed concurrently with the present application, the entirety of which is hereby incorporated by reference herein.

It is envisioned that the each cell 120 and the entire stent 100 can be of any reasonable dimension for the intended purpose of use within a patient's vasculature. Likewise, the total number of cells 120 can be of any reasonable value. Further, as shown in FIG. 4, connector members 180 may be included on stent 100 to temporarily secure stent 100 to a delivery device, for example.

In disclosed embodiments, the inside diameter of a preloaded stent 100 (i.e., prior to insertion into a catheter) is between about 0.5000 inches and about 0.6000 inches, and the inside diameter of a predeployed stent 100 (i.e., compacted within a catheter) is between about 0.0500 inches and about 0.0600 inches.

In use, stent 100 is advanced to a site in a bodily lumen. Stent 100 is then expanded at the site. Stent 100 may be expanded through any conventional means. For example, stent 100 may be placed on the balloon tip of a catheter. Here, the balloon is expanded at the site to generate radial forces on the interior of stent 100. The radial forces urge stent 100 to radially expand, e.g., without appreciable longitudinal expansion or contraction. Plastic deformation of the material of stent 100 (e.g., stainless steel) results in stent 100 retaining the expanded shape following subsequent deflation of the balloon. Alternatively, the stent 100 may be formed of a super-elastic or shape memory material (e.g., nitinol).

Numerous modifications are possible. For example stent 100 may be lined with either an inner or outer sleeve (such as polyester fabric or ePTFE) to facilitate tissue growth. Also, at least a portion of stent 100 may be coated with radiopaque coatings such as platinum, gold, tungsten or tantalum. In addition to materials previously discussed, stent 100 may be formed of other materials, including, without limitation, MP35N, tantalum, platinum, gold, Elgiloy and Phynox.

While three cells 120 are shown in FIG. 4 circumferentially connected along the diameter of stent 100, a different number could be so connected to vary the properties of stent 100 as a designer may elect. Likewise, while each column of cells 120 in FIG. 4 is shown as having three circumferentially connected cells 120, the number of circumferentially connected cells 120 could vary to adjust the properties of stent 100.

When forming stent 100 from shape memory metal such as nitinol, stent 100 can be laser cut from a nitinol tube. Thereafter, stent 100 can be subjected to a shape-setting process in which the cut tube is expanded on a mandrel and then heated. Multiple expansion and heating cycles can be used to shape-set stent 100 to the final expanded diameter. It is envisioned that the final expanded diameter is equal to the desired deployed diameter of stent 100. During expansion, it is envisioned that stent 100 is axially restrained such that the length of stent 100 does not change during expansion. It is further envisioned that the finished stent 100 has an austenite finish temperature less than body temperature. Here, at body temperature, stent 100 will self-expand to the desired deployed diameter due to the shape memory characteristic of the metal forming stent 100.

In use, stent 100 can be mounted on a delivery catheter. As is conventionally known in the art, stent 100 can be held in a compressed orientation on the delivery catheter by a retractable sheath. As is also known in the art, the delivery catheter can be used to advance stent 100 to a deployment location (e.g., a constricted region of a vessel). At the deployment site, the sheath is retracted thereby releasing stent 100. Once released, stent 100 self-expands to the deployed diameter. While an envisioned use for the features disclosed in the accompanying figures relates to that of a self-expanding stent, the features also have benefits when used with non-self-expanding stents (e.g., balloon expandable stents made of a material such as stainless steel).

From the foregoing and with reference to the various figure drawings, those skilled in the art will appreciate that certain modifications can also be made to the present disclosure without departing from the scope of the same. It is not intended that the disclosure be limited to the embodiments shown in the accompanying figures, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto. 

1. A stent comprising: a stent body defining a length and comprising a plurality of cells, each cell comprising two structural members extending in an undulating pattern, and each structural member comprising a plurality of cell segments defining a plurality of nodes therebetween, wherein the radius of curvature of a first node is different from a radius of curvature of a second node, and wherein the radius of curvature of the first node is between about 250% and about 700% larger than the radius of curvature of the second node.
 2. (canceled)
 3. The stent of claim 1, wherein the radius of curvature of the first node is between about 500% and about 600% larger than the radius of curvature of the second node.
 4. The stent of claim 1, wherein the radius of curvature of the first node is about 250% larger than the radius of curvature of the second node.
 5. The stent of claim 1, wherein the radius of curvature of the first node is between about 0.0030 inches and about 0.0040 inches.
 6. The stent of claim 5, wherein the radius of curvature of the second node is between about 0.0001 inches and about 0.0010 inches. 7-17. (canceled)
 18. The stent of claim 1, wherein, when the stent is deformed, a peak strain at the first node is greater than a peak strain at the second node.
 19. The stent of claim 1, wherein the stent body exhibits a predeployed inside diameter of between about 0.0500 inches and about 0.0600 inches.
 20. The stent of claim 1, wherein at least one of the radius of curvature of the first node or the radius of curvature of the second node is a non-constant radius of curvature.
 21. A method comprising: inserting a stent into a body lumen of a patient when the stent is in a predeployed configuration; and deploying the stent to an expanded configuration while in the body lumen, wherein the stent includes: a stent body defining a length and comprising a plurality of cells, each cell comprising two structural members extending in an undulating pattern, and each structural member comprising a plurality of cell segments defining a plurality of nodes therebetween, wherein the radius of curvature of a first node is different from a radius of curvature of a second node, and wherein the radius of curvature of the first node is between about 250% and about 700% larger than the radius of curvature of the second node.
 22. The method of claim 21, wherein the radius of curvature of the first node is between about 500% and about 600% larger than the radius of curvature of the second node.
 23. The method of claim 21, wherein the radius of curvature of the first node is about 250% larger than the radius of curvature of the second node.
 24. The method of claim 21, wherein the radius of curvature of the first node is between about 0.0030 inches and about 0.0040 inches.
 25. The method of claim 21, wherein the radius of curvature of the second node is between about 0.0001 inches and about 0.001 0 inches.
 26. The method of claim 21, wherein, when the stent is deformed, a peak strain at the first node is greater than a peak strain at the second node.
 27. The method of claim 21, wherein the stent body exhibits a predeployed inside diameter of between about 0.0500 inches and about 0.0600 inches.
 28. The method of claim 21, wherein at least one of the radius of curvature of the first node or the radius of curvature of the second node is a non-constant radius of curvature.
 29. The method of claim 22, wherein the body lumen of the patient comprises a vasculature of the patient. 